Photoacoustic image generation apparatus and method

ABSTRACT

After light has been output to a subject to be examined, a photoacoustic wave induced in the subject by the output light is detected. It is assumed that at least one virtual detector element is present outside of a real detector, and dummy data corresponding to the at least one virtual detector element are added to photoacoustic data in which pieces of data of the photoacoustic wave detected by the detector are arranged in accordance with the positions of detector elements. A photoacoustic image is generated by reconstructing the photoacoustic data to which the dummy data have been added by using a Fourier transform method.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a Continuation of PCT International Application No.PCT/JP2013/004864 filed on Aug. 15, 2013, which claims priority under 35U.S.C. §119(a) to Japanese Patent Application No. 2012-180723 filed onAug. 17, 2012 and Japanese Patent Application No. 2013-168095 filed onAug. 13, 2013. Each of the above applications is hereby expresslyincorporated by reference, in its entirety, into the presentapplication.

BACKGROUND OF THE INVENTION

Field of the Invention

The present invention relates to a photoacoustic image generationapparatus and method, and particularly to a photoacoustic imagegeneration apparatus and method that detects, after light has beenoutput to a subject to be examined, a photoacoustic wave induced in thesubject to be examined, and generates a photoacoustic image.

Description of the Related Art

Ultrasonography is known as one of image examination methods that canperform non-invasive examination to find the condition of the inside ofa living body. In ultrasonography, an ultrasonic probe that can send andreceive ultrasounds is used. When an ultrasound is sent from theultrasonic probe to the subject to be examined (living body), theultrasound travels in the living body and is reflected at a tissueinterface. The reflected ultrasound is received by the ultrasonic probe.It is possible to generate an image representing the state of the insideof the subject to be examined by calculating a distance based on thelength of time till the reflected ultrasound returns to the ultrasonicprobe.

Further, photoacoustic imaging, which images the inside of a living bodyby utilizing photoacoustic effects, is known. Generally, inphotoacoustic imaging, pulsed laser light, such as a laser pulse, isoutput to the inside of the living body. In the inside of the livingbody, living tissue absorbs energy of the pulsed laser light, and anultrasound (photoacoustic signals) is induced by adiabatic expansioncaused by the energy. The photoacoustic signals are detected by anultrasonic probe or the like, and a photoacoustic image is constructedbased on the detected signals. Accordingly, it is possible to visualizethe inside of the living body based on the photoacoustic signals.

Here, in generation of an ultrasonic image and a photoacoustic image,image reconstruction methods are roughly classifiable into two kinds ofmethod, i.e., a time domain method and a Fourier domain method (Fouriertransform method). The time domain method utilizes the feature that asonic wave is a spherical wave, and draws candidates of a sonic wavesource in real space. Typical examples of the time domain method are aDnS (Delay and Sum) method, and a CBP (Circular Back Projection) method,and an HTA (Hough Transform Algorithm) method.

Meanwhile, image reconstruction by the Fourier transform method (FTA(Fourier Transform Analysis) method) utilizes the feature that measuredinformation in time space is able to be transformed to information inreal space by using Fourier transform and dispersion relations of sonicwaves. Specifically, first, a spectrum in time scale is obtained byperforming forward Fourier transform on a time series of measured sonicwaves. Then, transformation from time scale to space scale is performedbased on the dispersion relations of sonic waves (ω=ck, ω: temporalfrequency, and k: spatial frequency), and after then, inverse Fouriertransform is performed. Accordingly, the spatial distribution of sonicwave sources is obtained as an image.

Japanese Unexamined Patent Publication No. 2010-035806 (PatentDocument 1) discloses generation of a photoacoustic image by utilizingimage reconstruction by the time domain method and image reconstructionby the Fourier transform method. In the image reconstructed by using thetime domain method and the image reconstructed by using the Fouriertransform method, artifacts appear in different manners from each other.Patent Document 1 utilizes such characteristics, and obtains aphotoacoustic image in which artifacts are suppressed by combining theimages reconstructed by using the two different methods.

SUMMARY OF THE INVENTION

Ultrasonic imaging and photoacoustic imaging differ from each other inthat a reflection ultrasound induced at a position to which anultrasound has been sent is detected in ultrasonic imaging while aphotoacoustic wave induced at a position that has been illuminated withlight is detected in photoacoustic imaging. In photoacoustic imaging,light is output not only to a region of a subject to be examinedcorresponding to an area in which detector elements of an ultrasonicdetector are present, in other words, a region of a subject to beexamined to which an area in which the detector elements are present isprojected, perpendicularly to an ultrasound detection surface, in thedepth direction of the subject to be examined. The light is often outputalso to a region of the subject to be examined outside of the regioncorresponding to the area in which the detector elements are present. Inthat case, a photoacoustic wave from the region outside of the regioncorresponding to the device area of the photoacoustic wave detector isdetected, especially, at end parts of the device area. Whenphotoacoustic signals including a detection signal of such aphotoacoustic wave are reconstructed by using a Fourier transformmethod, light absorbing material outside of the device area is foldedover into the device area, and that has caused an artifact in somecases. In Patent Document 1, the photoacoustic image generated by theFourier transform method is combined with a photoacoustic imagegenerated by the time domain method. Consequently, it is possible toreduce an influence of the artifact present in the photoacoustic imagegenerated by the Fourier transform method. However, it is impossible tosuppress the artifact, itself, present in the photoacoustic imagegenerated by using the Fourier transform method.

In view of the foregoing circumstances, it is an object of the presentinvention to provide a photoacoustic image generation apparatus andmethod that can suppress artifacts caused by a photoacoustic wave from aregion outside of a region that corresponds to a device area when aphotoacoustic image is generated by using the Fourier transform method.

To achieve the aforementioned object, the present invention provides aphotoacoustic image generation apparatus including an acoustic wavedetection means that includes a plurality of detector elements that areat least linearly arranged, and detects, after light has been output toa subject to be examined, a photoacoustic wave induced in the subject bythe output light, a dummy data addition means that assumes that at leastone virtual detector element is present outside of the plurality ofdetector elements that are at least linearly arranged, and adds dummydata corresponding to the at least one virtual detector element tophotoacoustic data in which pieces of data of the photoacoustic wavedetected by the plurality of detector elements in the acoustic wavedetection, means, respectively, are arranged in accordance with thepositions of the detector elements, and an image generation means thatgenerates a photoacoustic image by reconstructing the photoacoustic datato which the dummy data have been added by using a Fourier transformmethod.

In the present invention, the number of the at least one virtualdetector element may be determined based on the element size of thedetector element in a direction of arrangement of the detector elementsin the acoustic wave detection means and a center frequency of thedetector elements.

The number of the at least one virtual detector element may bedetermined based on a length represented by D(f)×tan α, where an anglefrom a straight line perpendicular to an acoustic wave detection surfacein the acoustic wave detection means, and the angle being determinedbased on a product of the element size and the center frequency, is α,and the center frequency is f, and a depth determined based on thecenter frequency f is D(f).

The angle α may be determined based on a value obtained by dividing thesound velocity of an acoustic wave traveling in the subject to beexamined by the product of the element size and the center frequency.

The depth D(f) may represent a maximum depth at which a signal to noiseratio higher than a predetermined value is obtained when the detectorelements having the center frequency f are used.

The number of the at least one virtual detector element may bedetermined based on a value obtained by dividing the length representedby the product of D(f) and tan α by a channel pitch of the (virtual)detector elements.

The apparatus may further include an image mask means that masks, in thegenerated photoacoustic image, an area outside of a straight lineextending, at the angle α, from a pixel corresponding to a detectorelement at an end of the plurality of detector elements, which are atleast linearly arranged, toward an area in which the dummy data havebeen added.

The dummy data addition means may assume that the at least one virtualdetector element is present on both sides of the linearly arrangedplurality of detector elements in a direction of arrangement of thedetector elements, and add the dummy data.

The number of the at least one virtual detector element may bedetermined in advance for each acoustic detection means to be used.

The dummy data may be 0 (the value of zero).

The reconstruction by using the Fourier transform method includes, forexample, two-dimensional Fourier transform on the photoacoustic data towhich the dummy data have been added. In the reconstruction by using theFourier transform method, the reconstruction may be performed aftercomponents higher than or equal to a predetermined frequency in adirection of arrangement of the detector elements are cut in thephotoacoustic data on which the two-dimensional Fourier transform hasbeen performed.

The reconstruction by using the Fourier transform method may includetwo-dimensional inverse Fourier transform on the photoacoustic data onwhich the two-dimensional Fourier transform has been performed. Thetwo-dimensional inverse Fourier transform may be performed by performinginverse Fourier transform in the direction of arrangement of thedetector elements after performing inverse Fourier transform in adirection orthogonal to the direction of arrangement of the detectorelements.

Further, the present invention provides a photoacoustic image generationmethod including the step of detecting, after light has been output to asubject to be examined, a photoacoustic wave induced in the subject bythe output light by using an acoustic wave detection means including aplurality of detector elements that are at least linearly arranged, thestep of assuming that at least one virtual detector element is presentoutside of the plurality of detector elements that are at least linearlyarranged, and adding dummy data corresponding to the at least onevirtual detector element to photoacoustic data in which pieces of dataof the photoacoustic wave detected by the plurality of detector elementsin the acoustic wave detection means, respectively, are arranged inaccordance with the positions of the detector elements, and the step ofgenerating a photoacoustic image by reconstructing the photoacousticdata to which the dummy data have been added by using a Fouriertransform method.

The photoacoustic image generation apparatus and method of the presentinvention assumes that at least one virtual detector element is presentoutside of a plurality of detector elements that are at least linearlyarranged, and adds dummy data corresponding to the at least one virtualdetector element to real data of photoacoustic waves detected bydetector elements in the photoacoustic detection means. Further, aphotoacoustic image is generated from the photoacoustic data to whichthe dummy data have been added by using a Fourier transform method.Therefore, it is possible to reduce a wrap-around noise, which isproduced when reconstruction by the Fourier transform method isperformed without adding dummy data, and to obtain a photoacoustic imagein which artifacts are suppressed. Further, it is possible to increasethe width of the photoacoustic image in a lateral direction (a directionof arrangement of the detector elements) by a width corresponding theadded dummy data. Therefore, it is possible to generate an imagerepresenting a wider range of the subject to be examined.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a block diagram illustrating a photoacoustic image generationapparatus according to a first embodiment of the present invention:

FIG. 2 is a diagram illustrating photoacoustic data to which dummy datahave been added;

FIG. 3 is a diagram illustrating an example of a generated photoacousticimage;

FIG. 4 is a diagram illustrating a comparative example of photoacousticimage:

FIG. 5 is a flow chart showing operation procedures;

FIG. 6 is a diagram illustrating determination of the width of a dummydata addition area;

FIG. 7A is a diagram illustrating a photoacoustic image obtained byreconstructing data including dummy data:

FIG. 7B is a diagram illustrating a photoacoustic image obtained byreconstructing data including dummy data;

FIG. 8 is a graph showing a relationship between marginal angles atwhich light absorbing material is clearly visually recognizable and thevalues of Sound Velocity in Subject to be Examined/(Channel Pitch ofUltrasonic Transducers×Center Frequency);

FIG. 9 is a graph showing a relationship between center frequency f andmeasurable depth D(f);

FIG. 10 is a block diagram illustrating a photoacoustic image generationapparatus in a third embodiment of the present invention;

FIG. 11 is a diagram illustrating an area in which an image is masked;

FIG. 12 is a block diagram illustrating a photoacoustic imagereconstruction means in the third embodiment of the present invention;

FIG. 13 is a diagram illustrating photoacoustic data to which dummy datahave been added;

FIG. 14 is a diagram illustrating photoacoustic data in which highfrequency components have been cut;

FIG. 15 is a diagram illustrating a reconstruction image in whichtwo-dimensional inverse Fourier transform has been performed;

FIG. 16 is a diagram illustrating a photoacoustic image when highfrequency components have been cut in reconstruction;

FIG. 17 is a diagram illustrating a photoacoustic image when the highfrequency components are not cut; and

FIG. 18 is a diagram illustrating a differential image between thephotoacoustic image illustrated in FIG. 16 and the photoacoustic imageillustrated in FIG. 17.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

Next, with reference to drawings, embodiments of the present inventionwill be described in detail. In examples of the present invention, anultrasound is used as an acoustic wave. Alternatively, an acoustic wavehaving an audible frequency may be used by selecting an appropriatefrequency for a target of examination, a measurement condition and thelike.

FIG. 1 is a diagram illustrating a photoacoustic image generationapparatus according to a first embodiment of the present invention. Thephotoacoustic image generation apparatus (photoacoustic image diagnosisapparatus) 10 includes a probe (ultrasonic probe) 11, an ultrasonic unit12 and a laser unit (light source) 13. The laser unit 13 generates laserlight output to a subject to be examined, such as living body tissue.The wavelength of the laser light should be appropriately set based onliving body tissue or the like to be observed. The laser light outputfrom the laser unit 13 is, for example, guided to the probe 11 by alight guide means, such as an optical fiber. Here, it is not necessarythat the light output to the subject to be examined is laser light.Light other than the laser light may be output to the subject to beexamined.

The probe 11 is an acoustic wave detection means, and includes pluraldetector elements (ultrasonic transducers) that are at least linearlyarranged. The probe 11 detects, after light has been output to thesubject to be examined, a photoacoustic wave induced in the subject bythe output light. Further, the probe 11 includes a light output unit,and outputs, toward the subject to be examined, the light that has beenguided from the laser unit 13. It is not necessary that light is outputto the subject to be examined from the probe 11. The light may be outputto the subject to be examined from a position other than the probe 11.

The ultrasonic unit 12 includes a receiving circuit 21, an AD conversionmeans 22, a receiving memory 23, a dummy data addition means 24, animage generation means 25, a trigger control circuit 26 and a controlmeans 27. The receiving circuit 21 receives a detection signal(photoacoustic signal) of the photoacoustic wave detected by the probe11. The AD conversion means 22 converts the photoacoustic signalreceived by the receiving circuit 21 to a digital signal. For example,the AD conversion means 22 performs, based on an AD clock signal of apredetermined frequency, sampling on the photoacoustic signal at apredetermined sampling cycle. The receiving memory 23 stores thephotoacoustic signal on which sampling has been performed by the ADconversion means 22.

The dummy data addition means 24 reads out data of the photoacousticwave that has been detected by each ultrasonic transducer in the probe11 from the receiving memory 23. In the data of the photoacoustic wave(photoacoustic wave data) that have been read out, photoacoustic signalsdetected by the ultrasonic transducers, respectively, are arranged inaccordance with the positions of the ultrasonic transducers. The dummydata addition means 24 assumes that the probe 11 includes a virtualultrasonic transducer or transducers (virtual detector element orelements) outside of linearly-arranged plural ultrasonic transducers,and adds dummy data corresponding to the virtual ultrasonic transduceror transducers to the photoacoustic data. The value of the dummy data tobe added is 0 (a signal level is 0). The image generation means 25generates a photoacoustic image by reconstructing the photoacoustic datato which the dummy data have been added by using a Fourier transformmethod. The reconstruction by using the Fourier transform methodincludes two-dimensional Fourier transform on the photoacoustic data towhich dummy data have been added, transformation (mapping) from timescale to space scale on the data on which the Fourier transform has beenperformed, and two-dimensional inverse Fourier transform on the dataafter mapping.

FIG. 2 is a diagram illustrating photoacoustic data to which dummy datahave been added. A real data area 50 is an area in which signalsdetected by the ultrasonic transducers in the probe 11, respectively,and which have been read out from the receiving memory 23, are present.For example, when the probe 11 has 128 elements of ultrasonictransducer, the real data area 50 is an area corresponding to the 128elements. Meanwhile, dummy data 51 are data of dummy added to an areaoutside of the area in which the ultrasonic transducers of the probe 11are arranged, in other words, an area in which no correspondingultrasonic transducer is present in the real structure of the probe 11.

For example, the dummy data addition means 24 assumes that apredetermined number of element or elements of virtual ultrasonictransducer is present on each of both sides of the linearly-arrangedplural ultrasonic transducers in the direction of arrangement of theultrasonic transducers. Further, the dummy data addition means 24 addsdummy data 51 corresponding to the predetermined number of element orelements of virtual ultrasonic transducer to each of both sides of thereal data area 50. Specifically, dummy data 51 corresponding to 32elements of virtual ultrasonic transducer are added to each of bothsides of the real data area 50. Since the dummy data have been added,the photoacoustic data to which, the dummy data have been addedcorrespond to 192 elements while the number of ultrasonic transducersincluded in the real structure of the probe 11 is 128. Here, it is notnecessary that the dummy data 51 are added to both sides of the realdata area 50. The dummy data 51 may be added to one of the sides of thereal data area 50.

Back to FIG. 1, the image generation means 25 includes a photoacousticimage reconstruction means 251, a wave detection and logarithmictransform means 252 and a photoacoustic image configuration means 253.The photoacoustic image reconstruction means 251 performs imagereconstruction by using a Fourier transform method (FTA method) on thephotoacoustic data to which the dummy data have been added. The wavedetection and logarithmic transform means 252 obtains an envelope ofdata of each line that have been reconstructed by the photoacousticimage reconstruction means 251, and performs logarithmic transform onthe obtained envelope. The photoacoustic image configuration means 253generates a photoacoustic image based on data of each line on whichlogarithmic transform has been performed. For example, the photoacousticimage configuration means 253 generates the photoacoustic image bytransforming the position of the photoacoustic signal (peak part) in thedirection of a time axis to a position in the direction of a depth inthe photoacoustic image. The image display means 14 is an image displaydevice, such as a display device. The image display means 14 displaysthe generated photoacoustic image and the like.

The control means 27 controls each unit in the ultrasonic unit 12. Thetrigger control circuit 26 sends a flash lamp trigger signal to thelaser unit 13 when the photoacoustic image is generated. Further, thetrigger control circuit 26 sends a Q-switch trigger signal afteroutputting the flash lamp trigger signal. The laser unit 13 includes aflash lamp 31 and a Q-switch 32. When the laser unit 13 receives theflash lamp trigger signal, the laser unit 13 turns on the flash lamp 31,and starts excitation of the laser. When the Q-switch trigger signal isinput to the laser unit 13, the laser unit 13 turns on the Q-switch, andoutputs pulsed laser light. The trigger control circuit 26 sends asampling trigger signal to the AD conversion means 22 synchronously withoutput of laser light to the subject to be examined. Accordingly, thetrigger control circuit 26 controls the timing of starting sampling onthe photoacoustic signal in the AD conversion means 22.

FIG. 3 is a diagram illustrating an example of the generatedphotoacoustic image. The image illustrated in FIG. 3 is a photoacousticimage of a sample in which light absorbing material is arranged at equalintervals in the direction of arrangement of the ultrasonic transducersand in the direction of the depth of the subject to be examined. In FIG.3, boundaries between the real data area 50 (FIG. 2) and the dummy data51 are indicated by broken lines. A photoacoustic wave (spherical wave)from light absorbing material that is present in the real data area 50perpendicularly enters an ultrasonic transducer of the probe 11 that ispresent right above the light absorbing material. Further, thephotoacoustic wave obliquely enters ultrasonic transducers around theultrasonic transducer. Therefore, it is possible to clearly recognize,in the photoacoustic image, the light absorbing material that is presentin the real data area 50 by reconstructing the photoacoustic data.

Meanwhile, a photoacoustic wave from light absorbing material that ispresent in an area next to the real data area 50, and to which the dummydata 51 have been added, is not able to perpendicularly enter anyultrasonic transducer of the probe 11. The photoacoustic wave onlyobliquely enters an ultrasonic transducer or transducers at an end partor parts. In the embodiment of the present invention, the lightabsorbing material outside of the device area is represented in an imageby using the photoacoustic wave that has obliquely entered theultrasonic transducer or transducers at the end part or parts. Sincereconstruction is performed on data including the dummy data, it ispossible to generate, based on the photoacoustic wave that has enteredthe ultrasonic transducer or transducers at the end part or parts, animage representing the light absorbing material that is present in thearea to which the dummy data 51 have been added. Consequently, it ispossible to widen the field of view of the photoacoustic image (a rangerepresented in the image).

FIG. 4 is a diagram illustrating a comparative example of aphotoacoustic image that has been generated without adding any dummydata. The photoacoustic image illustrated in FIG. 4 is obtained byreconstructing data that are present in the real data area 50 when thephotoacoustic image illustrated in FIG. 3 is obtained by using a Fouriertransform method. The image size of the photoacoustic image (FIG. 3)obtained by performing reconstruction on data including the dummy data51 is, for example, 480×600 pixels, while the image size of thephotoacoustic image (FIG. 4) obtained by performing reconstruction onlyon the real data area 50 is, for example, 320×600 pixels.

When reconstruction of the image is performed without adding the dummydata 51, an area 61 part illustrated in FIG. 3 appears, as a wrap-aroundnoise, in an area 64 part illustrated in FIG. 4, and that causes anartifact. Further, an area 62 part illustrated in FIG. 3 appears, as awrap-around noise, in an area 63 part illustrated in FIG. 4, and thatcauses an artifact. When reconstruction by using a Fourier transformmethod is performed on data including the dummy data, it is possible toobtain a photoacoustic image, as illustrated in FIG. 3, in whichartifacts caused by the photoacoustic wave from an area outside of thereal data area 50 are suppressed.

FIG. 5 is a diagram illustrating operation procedures. The triggercontrol circuit 26 outputs a flash lamp trigger signal to the laser unit13. The laser unit 13 receives the flash lamp trigger signal, and turnson the flash lamp 31. The trigger control circuit 26 outputs a Q-switchtrigger signal at predetermined timing. When the Q-switch trigger signalis input, the laser unit 13 turns on the Q-switch 32, and outputs pulsedlaser light. The output pulsed laser light is, for example, guided tothe probe 11, and output from the probe 11 to the subject to be examined(step S1).

The probe 11 detects, after laser light is output, a photoacousticsignal induced in the subject by the laser light output to the subject(step S2). The receiving circuit 21 in the ultrasonic unit 12 receivesthe photoacoustic signal detected by the probe 11. The trigger controlcircuit 26 sends a sampling trigger signal to the AD conversion means 22in such a manner to be matched with the timing of outputting light tothe subject to be examined. The AD conversion means 22 receives thesampling trigger signal, and starts sampling on the photoacousticsignal. The AD conversion means 22 stores sampling data of thephotoacoustic signal in the receiving memory 23.

The dummy data addition means 24 reads out the sampling data of thephotoacoustic signal from the receiving memory 23, and adds dummy datato the sampling data (photoacoustic data) of the photoacoustic signal,which have been read out (step S3). When the dummy data addition means24 adds dummy data, the dummy data addition means 24 assumes, forexample, that a virtual ultrasonic transducer or transducers are presenton both sides of linearly arranged plural ultrasonic transducers of theprobe 11 in the direction of the arrangement of the plural ultrasonictransducers. Further, the dummy data addition means 24 adds “0” (dummydata), as a detection signal of a photoacoustic wave detected by thevirtual ultrasonic transducer or transducers.

The photoacoustic image reconstruction means 251 performs reconstructionby using a Fourier transform method on the photoacoustic data to whichthe dummy data have been added (step S4). The wave detection andlogarithmic transform means 252 obtains an envelope of data of each linethat have been obtained by reconstruction, and performs logarithmictransform on the obtained envelope. The photoacoustic imageconfiguration means 253 generates a photoacoustic image based on data ofeach line on which logarithmic transform has been performed (step S5).The image display means 14 displays the photoacoustic image that hasbeen generated in step S5 on a display screen (step S6).

In the embodiment of the present invention, it is assumed that thevirtual ultrasonic transducer or transducers are present outside of thelinearly-arranged plural ultrasonic transducers in the probe. Further,dummy data corresponding to the virtual ultrasonic transducer ortransducers are added to real data of the photoacoustic wave detected bythe ultrasonic transducers in the probe 11. Further, a photoacousticimage is generated from the photoacoustic data to which the dummy datahave been added by using a Fourier transform method. When thephotoacoustic image is generated in this manner, it is possible toreduce a wrap-around noise, which is generated when reconstruction isperformed by using the Fourier transform method without adding the dummydata. Therefore, it is possible to obtain a photoacoustic image in whichan artifact caused by a photoacoustic wave from a region outside of aregion that corresponds to the device area is suppressed. Further, it ispossible to increase the width of the photoacoustic image in a lateraldirection (the direction of arrangement of ultrasonic transducers) by awidth corresponding to the added dummy data. Therefore, it is possibleto generate an image representing a wider range of the subject to beexamined.

In detection of a photoacoustic wave, it is not necessary to use all ofthe ultrasonic transducers included in the probe 11. For example, aphotoacoustic wave may be detected by using a part of the ultrasonictransducers included in the probe 11 to increase a frame rate, or thelike. In such a case, the dummy data addition means 24 should add dummydata by assuming that a virtual ultrasonic transducer or transducers arepresent outside of an area in which ultrasonic transducers used indetection of the photoacoustic wave are present, in other words, an areain which data of the detected photoacoustic wave are present.

For example, when the probe 11 has 128 ultrasonic transducers that arelinearly arranged, detection of a photoacoustic wave may be performed byusing 64 of the ultrasonic transducers located at a center. In thiscase, 32 ultrasonic transducers on either side of the 64 ultrasonictransducers do not contribute to detection of the photoacoustic wave. Inthat case, the dummy data addition means 24 may assume that a virtualultrasonic transducer or transducers are present at a position that atleast partially overlaps with the area of the 32 ultrasonic transducerslocated on either side of the 64 ultrasonic transducers. Further, thedummy data addition means 24 may add the dummy data to the photoacousticdata that have been detected by the 64 photoacoustic transducers at thecenter. As this example shows, it is not necessary that the dummy dataaddition means 24 assumes that a virtual ultrasonic transducer ortransducers are present at a position in which no ultrasonic transduceris present in the real structure of the probe 11.

Next, a second embodiment of the present invention will be described.The configuration of a photoacoustic image generation apparatus in thepresent embodiment is similar to the configuration of the photoacousticimage generation apparatus 10 in the first embodiment, which isillustrated in FIG. 1. In the description of the first embodiment, thewidth of an area (dummy data addition area) to which dummy data areadded is a constant value. In the present embodiment, the width of thedummy data addition area is determined based on the characteristics ofthe subject to be examined and the probe 11. The second embodiment maybe similar to the first embodiment and the like except that the width ofthe dummy data addition area is variable.

It is considered that a range in which light absorbing material outsideof the device area is able to be represented in an image changesdepending on the sensitivity (sensitivity in receiving) of the probe 11with respect to an acoustic wave that obliquely enters the probe 11. Forexample, when a sensitivity of detection with respect to an acousticwave having an angular component greater than a certain angle is low, itis considered that the probe 11 is not able to detect a photoacousticwave from light absorbing material that is present in an area outside ofa straight line extending at the angle from an ultrasonic transducer atan end. Therefore, the width of the dummy data addition area should bedetermined based on the characteristics of detecting the acoustic wavein an oblique direction at the probe 11. Further, the acoustic waveattenuates more while the acoustic wave travels in the subject to beexamined, as the frequency is higher. Therefore, when the width of thedummy data addition area is determined, the center frequency (afrequency at which the sensitivity of detection is highest) of of thedetector elements should be considered.

The sensitivity in receiving in an oblique direction by the ultrasonictransducers in the probe 11 depends on Sound Velocity in Subject to beExamined/(Channel Pitch of Ultrasonic Transducers×Center Frequency).Here, the channel pitch of the ultrasonic transducers is defined by theelement size of the ultrasonic transducer (the width of the ultrasonictransducer in the direction of arrangement of the ultrasonictransducers). The center frequency is defined, for example, by thethickness of a thin film of the ultrasonic transducer consisting of PZT(Lead Zirconate Titanate) and the thickness of an acoustic matchinglayer or an acoustic impedance.

FIG. 6 is a diagram illustrating determination of the width of a dummydata addition area. The dummy data addition means 24 defines an anglewith respect to a straight line perpendicular to an ultrasonic detectionsurface of the probe 11, as angle α of increased field of view. Thedummy data addition means 24 determines, based on Sound Velocity inSubject to be Examined/(Channel Pitch of Ultrasonic Transducers×CenterFrequency), increased field of view α. Further, the dummy data additionmeans 24 determines measurable depth (the depth of a position) D(f)based on center frequency f. The dummy data addition means 24determines, as the width of the dummy data addition area, a length(width) greater than or equal to a value determined by D(f)×tan α. Thenumber of element or elements of virtual ultrasonic transducer assumedby the dummy data addition means 24 may be obtained, for example, bydividing the width of the dummy data addition area by the channel pitchof the ultrasonic transducers.

FIG. 7A and FIG. 7B are diagrams illustrating photoacoustic imagesobtained by reconstructing data including dummy data, respectively. FIG.7A illustrates a photoacoustic image when a photoacoustic wave has beendetected by using the probe 11 of Sound Velocity in Subject to beExamined/(Channel Pitch of Ultrasonic Transducers×CenterFrequency)=0.57. FIG. 7B illustrates a photoacoustic image when aphotoacoustic wave has been detected by using the probe 11 of SoundVelocity in Subject to be Examined/(Channel Pitch of UltrasonicTransducers×Center Frequency)=1.65.

In FIG. 7A, light absorbing material is clearly visually recognizable inan area inward (toward the device area) from a straight line 71extending, at the angle of 54° with respect to a direction perpendicularto an ultrasonic detection surface, from the position of an ultrasonictransducer at an end, as an origin, toward a dummy data addition areaside. However, light absorbing material is not clearly visuallyrecognizable in an area (toward an area opposite to the device area)outside of the straight line 71. Specifically, when the probe 11 ofSound Velocity in Subject to be Examined/(Channel Pitch of UltrasonicTransducers×Center Frequency)=0.57 is used, a marginal angle at whichlight absorbing material is clearly visually recognizable in the dummydata addition area is 54°.

In FIG. 7B, light absorbing material is clearly visually recognizable inan area inward from a straight line 72 extending, at the angle of 15°with respect to a direction perpendicular to an ultrasonic detectionsurface, from the position of an ultrasonic transducer at an end, as anorigin. However, light absorbing material is not clearly visuallyrecognizable in an area outside of the straight line 72. Specifically,when the probe 11 of Sound Velocity in Subject to be Examined/(ChannelPitch of Ultrasonic Transducers×Center Frequency)=1.65 is used, amarginal angle at which light absorbing material is clearly visuallyrecognizable in the dummy data addition area is 15°.

Photoacoustic images are generated by using plural probes 11 havingdifferent values of Sound Velocity in Subject to be Examined/(ChannelPitch of Ultrasonic Transducers×Center Frequency), and relationshipsbetween the values of Sound Velocity in Subject to be Examined/(ChannelPitch of Ultrasonic Transducers×Center Frequency) and marginal angles atwhich light absorbing material is clearly recognizable in the dummy dataaddition area are obtained in advance through experiments. The dummydata addition means 24 uses the relationships, and determines, based onthe value of Sound Velocity in Subject to be Examined/(Channel Pitch ofUltrasonic Transducers×Center Frequency) of the probe 11 used indetection of the photoacoustic wave, increased field of view α when thewidth of the dummy data addition area is determined.

FIG. 8 is a diagram illustrating a relationship between a marginal angleat which light absorbing material is clearly visually recognizable inthe dummy data addition area and Sound Velocity in Subject to beExamined/(Channel Pitch of Ultrasonic Transducers×Center Frequency). Inthe graph illustrated in FIG. 8, plotted points represent measuredvalues, and a straight line represents a relational expression obtainedfrom the measured values. For example, when a probe having the value ofSound Velocity in Subject to be Examined/(Channel Pitch of UltrasonicTransducers×Center Frequency) of 1 is used, the graph illustrated inFIG. 8 shows that the marginal angle at which light absorbing materialis clearly visually recognizable in the dummy data addition area isabout 35°. The dummy data addition means 24 determines that increasedfield of view α is 35° when the probe 11 of Sound Velocity in Subject tobe Examined/(Channel Pitch of Ultrasonic Transducers×Center Frequency)of 1 is used.

Measurable depth D(f) is obtainable as follows. For example, light isoutput to a sample in which light absorbing material is placed in thevicinity of a center of a device area, and a photoacoustic wave(photoacoustic signal) is detected by a probe 11 including ultrasonictransducers having certain center frequency f. A range in which a signalto noise ratio is higher than or equal to a predetermined value isstudied by detecting the photoacoustic signal while the position oflight absorbing material in the depth direction is changed. A maximumdepth in the range in which the signal to noise ratio is higher than orequal to a predetermined ratio is determined as measurable depth D(f).The aforementioned experiment is performed by using probes having pluralcenter frequencies f, and a relationship between the center frequencyand measurable depth D(f) is obtained.

FIG. 9 is a diagram illustrating a relationship between center frequencyf and measurable depth D(f). For example, a range of depth at which thesignal to noise ratio is 2 or higher is obtained with respect to pluralprobes 11 having different center frequencies from each other. Forexample, when detection of a photoacoustic wave is performed by using aprobe 11 including ultrasonic transducers having a center frequency of 3MHz, a photoacoustic signal is detectable at a signal to noise ratio of2 or higher in a range of 5 cm from the surface of the subject to beexamined. The dummy data addition means 24 determines that measurabledepth D(f) is 5 cm when the center frequency of the ultrasonictransducers is 3 MHz. Meanwhile, when detection of a photoacoustic waveis performed by using a probe 11 including ultrasonic transducers havinga center frequency of 9 MHz, a photoacoustic signal is detectable at asignal to noise ratio of 2 or higher in a range of 2 cm from the surfaceof the subject to be examined. The dummy data addition means 24determines that measurable depth D(f) is 2 cm when the center frequencyof the ultrasonic transducers is 9 MHz. The width of the dummy dataaddition area is obtainable by obtaining the product of measurable depthD(f) determined in this manner and tan α (FIG. 6).

The sound velocity in the subject to be examined is a constant valuewhen the subject to be examined is determined. Therefore, the soundvelocity may be regarded as a constant, and the width of the dummy dataaddition area (the number of element or elements of virtual ultrasonictransducer) may be determined based the channel pitch of the ultrasonictransducers and the center frequency. More specifically, increased fieldof view α may be determined based on the product of the channel pitch(element size) of ultrasonic transducers and the center frequency.Further, the width of the dummy data addition area may be determinedbased on the increased field of view α and measurable depth D(f), whichis a function of center frequency f. Alternatively, measurable depthD(f) may be a constant value (fixed value) instead of the function ofcenter frequency f.

In the embodiment of the present invention, the width of the dummy dataaddition area is determined based on the characteristic of the probe 11.The width of the dummy data addition area is determined, especially,based on the sensitivity of receiving in an oblique direction of theprobe 11 to be used. When the width of the dummy data addition area is afixed width, dummy data are added, in some cases, also to an area thatis not able to be represented in an image by the probe 11 used in theoperation. When reconstruction is performed by adding dummy data also tothe range that is not able to be represented in the image, a calculationtime unnecessarily becomes long. In the embodiment of the presentinvention, the width of the dummy data addition area is determinablebased on the characteristic of the probe 11. Therefore, it is possibleto prevent addition of the dummy data even to an area in which lightabsorbing material is not clearly visually recognizable in aphotoacoustic image after reconstruction. Hence, it is possible to avoidperforming unnecessary calculations.

Next, a third embodiment of the present invention will be described.FIG. 10 is a diagram illustrating a, photoacoustic image generationapparatus according to the third embodiment of the present invention. Aphotoacoustic image generation apparatus 10 a in the embodiment of thepresent invention includes an image mask means 28 in addition to thecomposition of the photoacoustic image generation apparatus 10illustrated in FIG. 1. The image mask means 28 masks an area in thegenerated photoacoustic image outside of a straight line extending, atincreased field of view α, which has been described in the secondembodiment, from a pixel corresponding to an ultrasonic transducer at anend of the probe 11 toward an area in which the dummy data have beenadded. Other features may be similar to the second embodiment.

FIG. 11 is a diagram illustrating an area in which an image is masked.An area corresponding to a real data area 50 of a photoacoustic image isexcluded from an area to be masked. In the area in which the dummy data51 have been added, an area in which light absorbing material is notclearly visually recognizable is determined as an area 53 to be masked.Specifically, when the width of the dummy data addition area has beendetermined by measurable depth D(f)×tan α, an area toward the outside(toward an area opposite to the device area) from a straight lineextending, at angle α, from a pixel (a pixel at a boundary to an area towhich the dummy data 51 are added) at an end of the real data area 50,as an origin, toward the dummy data addition area side is determined asthe area 53 to be masked. The area 53 to be masked may be displayed, forexample, by displaying in the same manner as display of a signal levelof 0 (for example, black), or by displaying the same manner as displayof a background (for example, white).

In the embodiment of the present invention, display of an area outsideof a line at angle α in the dummy data addition area is masked. Since anarea in which light absorbing material is not clearly visuallyrecognizable is masked, it is possible to prevent an area containingonly noise components from being displayed. Other effects are similar tothe second embodiment.

Next, a fourth embodiment of the present invention will be described.FIG. 12 is a diagram illustrating a photoacoustic image reconstructionmans 251 in a photoacoustic image generation apparatus in the fourthembodiment of the present invention. In the embodiment of the presentinvention, the photoacoustic image reconstruction means 251 includes atwo-dimensional Fourier transform means 511, a filter means 512, amapping means 513 and a two-dimensional inverse Fourier transform means514. The photoacoustic image reconstruction means 251 may be configuredin a similar manner to the photoacoustic image generation apparatus inthe first embodiment, illustrated in FIG. 1, or the photoacoustic imagegeneration apparatus in the third embodiment, illustrated in FIG. 10.

The two-dimensional Fourier transform means 511 performs two-dimensionalFourier transform on the photoacoustic data to which the dummy data havebeen added by the dummy data addition means 24 (FIG. 1). As an algorithmof Fourier transform, for example, an algorithm of fast Fouriertransform may be used. The filter means 512 is a high-cut filter. Thefilter means 512 cuts components higher than or equal to a predeterminedfrequency in the direction of arrangement of ultrasonic transducers inthe probe 11 in the data on which two-dimensional Fourier transform hasbeen performed by the two-dimensional Fourier transform means 511.

The mapping means 513 performs transformation between time scale andspace scale based on the dispersion relations of sonic waves (ω=ck, ω:temporal frequency, and k: spatial frequency). The mapping means 513performs transformation between time scale and space scale, for example,by performing linear interpolation mapping on photoacoustic data onwhich Fourier transform has been performed. The two-dimensional inverseFourier transform means 514 performs two-dimensional inverse Fouriertransform on data that have been transformed by the mapping means 513.The two-dimensional inverse Fourier transform means 514 performs inverseFourier transform in a direction orthogonal to the direction ofarrangement of ultrasonic transducers. After then, the two-dimensionalinverse Fourier transform means 514 performs inverse Fourier transformin the direction of arrangement of the ultrasonic transducers.

FIG. 13 is a diagram illustrating photoacoustic data to which the dummydata have been added. The real data area 50 is an area of photoacousticdata detected by the probe 11. Dummy data 51 are data that have beenadded by the dummy data addition means 24. For example, the first columnthrough the N-th column correspond to the real data area 50, and the(N+1)th column through the 2N-th column correspond to the dummy data 51.The number of data points in each column is assumed to be M. Thetwo-dimensional Fourier transform means 511 performs two-dimensionalFourier transform, for example, on photoacoustic data of 2N columns×Mrows, to which dummy data have been added, as illustrated in FIG. 13.

FIG. 14 is a diagram illustrating photoacoustic data in which highfrequency components have been cut by the filter means 512. The filtermeans 512 cuts high frequency components by replacing high frequencycomponents in the direction of arrangement of the ultrasonic transducersof the data on which two-dimensional Fourier transform has beenperformed with 0. A cutoff position may be, for example, N/4 throughN/2. For example, when the cutoff position is N/2, the filter means 512replaces data in the range of N/2-th column through 3N/2-th column with0. The mapping means 513 performs mapping by linear interpolation foreach column on data in which high frequency components have been cut, asillustrated in FIG. 14. At this time, interpolation processing is notneeded, as for a column or columns of data set to “0”. Therefore, it ispossible to increase the speed of operation processing.

FIG. 15 is a diagram illustrating a reconstructed image on whichtwo-dimensional inverse Fourier transform has been performed. Thetwo-dimensional inverse Fourier transform means 514 generates areconstructed image by performing two-dimensional inverse Fouriertransform on data on, which matching has been performed by the matchingmeans 513. In two-dimensional inverse Fourier transform, first, Fourierinverse transform is performed for each column. At this time, processingis not needed as for a column or columns of data set to “0”. Therefore,it is possible to increase the speed of operation processing. Thetwo-dimensional inverse Fourier transform means 514 performs inverseFourier transform on each row after performing inverse Fourier transformon each column. The size of the reconstructed image in the direction ofarrangement of the ultrasonic transducers is extended by a sizecorresponding to the added dummy data. When an image is displayed, therange of 3N/2 through 2N should be arranged toward the left side of the0-th column facing the paper.

FIG. 16 is a diagram illustrating a photoacoustic image when highfrequency components have been cut in reconstruction. Here, a cutoffposition is assumed to be N/4. FIG. 17 is a diagram illustrating aphotoacoustic image when high frequency components are not cut. FIG. 18is a diagram illustrating a differential image between the photoacousticimage illustrated in FIG. 16 and the photoacoustic image illustrated inFIG. 17. Since the high frequency components were cut, it was possibleto reduce the noise components by a component corresponding to thedifferential image illustrated in FIG. 18.

In the embodiment of the present invention, high frequency components inthe direction of arrangement of ultrasonic transducers in the data onwhich two-dimensional Fourier transform has been performed are cut inreconstruction by using a Fourier transform method. Since the highfrequency components are cut, it is possible to reduce the noisecomponent. Further, since the high frequency components are cut, andlinear interpolation mapping is performed after data of a column orcolumns corresponding to the high frequency components are replaced with0, it is possible to reduce a target of processing when mapping isperformed. Hence, it is possible to increase the speed of processing.Further, in two-dimensional inverse Fourier transform, when inverseFourier transform on each column is performed first, processing on acolumn or columns in which data have been replaced with 0 is not needed.Therefore, it is possible to increase the speed of processing.

In the descriptions of each of the aforementioned embodiments, thephotoacoustic image reconstruction means 251 was assumed to performtwo-dimensional Fourier transform on photoacoustic data corresponding toa cross section. However, it is not necessary that processing isperformed in such a manner. Alternatively, an image may be reconstructedby performing three-dimensional Fourier transform on photoacousticvolume data. Further, the probe 11 in which plural ultrasonictransducers are two-dimensionally arranged may be used.

The number of virtual ultrasonic transducers (the width of dummy dataaddition area) that are assumed to be present by the dummy data additionmeans 24 may be determined, in advance, for each probe to be used. Forexample, the dummy data addition means 24 stores the kind of a probe 11(ID: identifier) and the number of virtual ultrasonic transducers whenthe probe 11 with the ID is used in such a manner to be correlated toeach other. After the probe 11 is connected to the ultrasonic unit 12,the dummy data addition means 24 obtains an ID of the probe 11 from theprobe 11. The dummy data addition means 24 may add dummy data byassuming that the same number of virtual ultrasonic transducer ortransducers as the number stored in such a manner to be correlated tothe ID obtained from the probe 11 are present.

In the third embodiment, a case in which display outside of angle α ismasked when the width of the dummy data addition area is variable hasbeen described. However, it is not necessary that the display is maskedin such a manner. Alternatively, in the first embodiment in which thewidth of the dummy data addition area is constant, increased field ofview α may be obtained based on the value of Sound Velocity in Subjectto be Examined/(Channel Pitch of Ultrasonic Transducers×CenterFrequency). Further, display outside of the obtained angle α may bemasked.

So far, the present invention has been described based on preferableembodiments. However, the photoacoustic image generation apparatus andmethod of the present invention is not limited to the aforementionedembodiments. Various modifications and changes are possible withoutdeparting from the scope of the present invention.

What is claimed is:
 1. A photoacoustic image generation apparatuscomprising: an acoustic wave detector that includes a plurality ofdetector elements arranged in a line, and detects, after light has beenoutput to a subject to be examined, a photoacoustic wave induced in thesubject by the output light; a dummy data adder that adds dummy datacorresponding to the at least one virtual detector element tophotoacoustic data in which pieces of data of the photoacoustic wavedetected by the plurality of detector elements in the acoustic wavedetector, respectively; and an image generator that generates aphotoacoustic image by reconstructing the photoacoustic data to whichthe dummy data have been added by using a two-dimensional Fouriertransform method, wherein the reconstruction by using the Fouriertransform method includes performing two-dimensional Fourier transformon the photoacoustic data to which the dummy data have been added andperforming two-dimensional inverse Fourier transform on thephotoacoustic data on which the two-dimensional Fourier transform hasbeen performed, wherein the at least one of virtual detector element isarranged by a channel pitch, which is the same as a channel pitch of thedetector elements in the acoustic wave detector, outside of anarrangement of the plurality of detector elements in a direction ofarrangement of the detector elements along with the line of the detectorelements, and wherein the photoacoustic data to which the dummy datahave been added in which pieces of data detected by each the detectorelements and pieces of data added for the at least one of virtualdetector element are arranged in accordance with the positions of thedetector elements and the positions of the at least one of the virtualdetector element in the line, respectively where an angle from astraight line perpendicular to an acoustic wave detection surface of theacoustic wave detector is α and the center frequency is f, and a depthdetermined based on the center frequency f is D(f), the angle α isdetermined based on a value obtained by dividing the sound velocity ofan acoustic wave traveling in the subject to be examined by the productof the channel pitch of the detector elements and the center frequencyof the detector elements, the number of the at least one virtualdetector element is determined such that the at least one virtualdetector elements is arranged at the channel pitch within a lengthrepresented by a product of D(f) and tan α; an image masker that masks amask area in the generated photoacoustic image, wherein the mask area isan area from a mask line, which includes a pixel corresponding thedetector element of the end of the detector elements arranged in theline, toward opposite to an area including pixels corresponding thedetector elements arranged in the line, the mask line is a straight lineextending at the angle a from a straight line in the photoacoustic imagecorresponding to a straight line perpendicular to an acoustic wavedetection surface of the acoustic wave detector and extending outside anreal data area in the photoacoustic image, wherein the real data area isan area generated from the photoacoustic data obtained by the detectorelements.
 2. The photoacoustic image generation apparatus, as defined inclaim 1, wherein the depth D(f) represents a maximum depth which isdetermined by detecting a photoacoustic signal in plural positions in adepth direction of a sample subject with the detector elements havingthe center frequency f and specifying at least one of signal to noiseratio higher than a predetermined value from the detected photoacousticsignals and obtaining at least one of depth corresponding to the atleast one of signal and determining the maximum depth of the obtained atleast one of depth.
 3. The photoacoustic image generation apparatus, asdefined in claim 1, wherein the number of the at least one virtualdetector element is determined based on a value obtained by dividing thelength represented by the product of D(f) and tan α by a channel pitchof the detector elements in the acoustic wave detector.
 4. Thephotoacoustic image generation apparatus, as defined in claim 1, whereinthe dummy data adder assumes that the at least one virtual detectorelement is present on both sides of a linearly arranged plurality ofdetector elements in the direction of arrangement of the detectorelements.
 5. The photoacoustic image generation apparatus, as defined inclaim 1, wherein the number of the at least one virtual detector elementis determined in advance for each acoustic detector to be used.
 6. Thephotoacoustic image generation apparatus, as defined in claim 1, whereinthe dummy data are
 0. 7. The photoacoustic image generation apparatus,as defined in claim 1, wherein the reconstruction by using the Fouriertransform method includes: performing two-dimensional Fourier transformon the photoacoustic data to which the dummy data have been added,cutting components higher than or equal to a predetermined frequency ina direction of arrangement of the detector elements in the photoacousticdata on which the two-dimensional Fourier transform has been performed,and performing two-dimensional inverse Fourier transform on thephotoacoustic data on which the components has been cut.
 8. Thephotoacoustic image generation apparatus, as defined in claim 7, whereinthe two-dimensional inverse Fourier transform is performed by performingone-dimensional inverse Fourier transform in the direction ofarrangement of the detector elements after performing one-dimensionalinverse Fourier transform in a direction orthogonal to the direction ofarrangement of the detector elements.
 9. A photoacoustic imagegeneration method comprising the steps of: detecting, after light hasbeen output to a subject to be examined, a photoacoustic wave induced inthe subject by the output light by using an acoustic wave detectorincluding a plurality of detector elements arranged in a line; addingdummy data corresponding to the at least one virtual detector element tophotoacoustic data in which pieces of data of the photoacoustic wavedetected by the plurality of detector elements in the acoustic wavedetector, respectively; generating a photoacoustic image byreconstructing the photoacoustic data to which the dummy data have beenadded by using a two-dimensional Fourier transform method; and masking amask area in the generated photoacoustic image, wherein thereconstruction by using the Fourier transform method includes performingtwo-dimensional Fourier transform on the photoacoustic data to which thedummy data have been added and performing two-dimensional inverseFourier transform on the photoacoustic data on which the two-dimensionalFourier transform has been performed; wherein the at least one ofvirtual detector element is arranged by a channel pitch, which is thesame as a channel pitch of the detector elements in the acoustic wavedetector, outside of an arrangement of the plurality of detectorelements in a direction of arrangement of the detector elements alongwith the line of the detector elements; wherein the photoacoustic datato which the dummy data have been added in which pieces of data detectedb each the detector elements and pieces of data added for the at leastone of virtual detector element are arranged in accordance with thepositions of the detector elements and the positions of the at least oneof the virtual detector element in the line, respectively where an anglefrom a straight line perpendicular to an acoustic wave detection surfaceof the acoustic wave detector is α and the center frequency is f, and adepth determined based on the center frequency f is D(f), the angle α isdetermined based on a value obtained by dividing the sound velocity ofan acoustic wave traveling in the subject to be examined by the productof the channel pitch of the detector elements and the center frequencyof the detector elements, the number of the at least one virtualdetector element is determined such that the at least one virtualdetector elements is arranged at the channel pitch within a lengthrepresented by a product of D(f) and tanα; and wherein the mask area isan area from a mask line, which includes a pixel corresponding thedetector element of the end of the detector elements arranged in theline, toward opposite to an area including pixels corresponding thedetector elements arranged in the line, the mask line is a straight lineextending at the angle a from a straight line in the photoacoustic imagecorresponding to a straight line perpendicular to an acoustic wavedetection surface of the acoustic wave detector and extending outside anreal data area in the photoacoustic image, wherein the real data area isan area generated from the photoacoustic data obtained by the detectorelements.
 10. The photoacoustic image generation method, as defined inclaim 3, wherein the number of the at least one virtual detector elementis determined based on a value obtained by dividing the lengthrepresented by the product of D(f) and tan α by a channel pitch of thedetector elements in the acoustic wave detector.
 11. The photoacousticimage generation method, as defined in claim 9, wherein in the step ofadding the dummy data, it is assumed that the at least one virtualdetector element is present on both sides of a linearly arrangedplurality of detector elements in the direction of arrangement of thedetector elements.